Mechanical transfection devices and methods

ABSTRACT

A transfection device suitable for delivery of various macrostructures (e.g., mitochondria, bacteria, liposomes) is described and uses mechanical force to thereby induce active endocytosis in a target cell. Contemplated devices are able to achieve high throughput of transfected cells that remain viable and are capable of producing colonies.

This application claims priority to our copending U.S. provisional application having Ser. No. 62/020,910, filed Jul. 3, 2014, which is incorporated by reference herein.

FIELD OF THE INVENTION

The field of the invention is cellular cargo delivery technologies.

BACKGROUND

The background description includes information that may be useful in understanding the present invention. It is not an admission that any of the information provided herein is prior art or relevant to the presently claimed invention, or that any publication specifically or implicitly referenced is prior art.

All publications identified herein are incorporated by reference to the same extent as if each individual publication or patent application were specifically and individually indicated to be incorporated by reference. Where a definition or use of a term in an incorporated reference is inconsistent or contrary to the definition of that term provided herein, the definition of that term provided herein applies and the definition of that term in the reference does not apply.

Transfection processes are used to deliver various types of materials into a cell, and there are numerous known methods in the art. For example, U.S. Pat. No. 5,586,982 describes a treatment device capable of delivering genetic material or drugs into cells of a patient in vivo using heat to assist with transfection. Unfortunately, such approach often tends to damage the cells. Moreover, since the poration lasts only for a very short time, the amount of material delivered into the cells will in most cases be significantly reduced, especially where the material is relatively large. Finally, such approach also fails to provide a method for culturing cells after transfection.

In another example, as described in US 2009/0081750, magnetic fields are employed to move cells through a channel in which the cells undergo transfection. Actual transfection is then performed via several possible manners, including electroporation, heat, or light. Similar to the '982 reference, effective transfection is typically limited to relatively small molecules and low quantities. Yet another example of poration to transfect cells is described in WO 2013/059343. Here, cells are fed through a microfluidic channel in a buffer that contains a delivery material. The cells pass through a constriction region, which causes the cells to become perturbed with pores through which the delivery material then diffuses. While this approach overcomes to at least some degree issues associated with short pulse time, delivery still requires poration.

A more extreme approach is presented in U.S. Pat. No. 5,858,663 in which a cold gas shockwave is used to accelerate micro projectiles that carry matter into the cells. While such approach guarantees delivery of even relatively large molecules into a cell, it is readily apparent that such approach is also prone to significantly damage a cell.

WO 96/24360 attempts to overcome shockwave damage by providing a time-dependent impulse transient characterized by rise time and magnitude that is thought to increase the overall permeability of a cell membrane, which results in an increase in diffusion of materials into the cell. The impulse is achieved by applying an optical field to a film on which the cells are grown, and the optical field ablates the film thereby delivering the impulse. While such approach will provide for transfection, high throughput production of transfected cells remains problematic. To increase throughput, WO 02/42447 teaches use of leverages shock or other forms of pressure, and U.S. Pat. No. 7,687,267 describes a high throughput cell transfection device for transfer of small nucleic acid molecules (e.g., DNA, siRNA) through electroporation where the device contains an array of cell transfection units. Similarly, US 2012/0244593 teaches a high throughput electroporation transfection device, which requires poration (i.e., electroporation) and diffusion to deliver the material.

Interestingly, the known transfection devices require significant disruption to a cellular membrane to allow for greater diffusion of cargo material, which becomes especially difficult where the cargo material is relatively large. Therefore, there is a need for improved transfection devices and methods suitable for delivery of cargo of various sizes, and especially large cargo of 1 μm or larger, through a cellular membrane that will not or only minimally adversely affect the cell.

SUMMARY OF THE INVENTION

The inventive subject matter is directed to transfection devices in which a macrostructure is delivered under pressure from a deformable fluid reservoir to cells contained in a container. Most preferably, the deformable fluid reservoir is coupled to the container via a microporous membrane having a pore size suitable to deliver the macrostructure to the cell, which is thought to internalize the macrostructure via active endocytosis. Such devices are characterized by their high transfection efficiency and low rate of cell damage.

In one aspect of the inventive subject matter, a transfection device is contemplated that includes a stage that receives and retains a container, and a deformable fluid reservoir is fluidly coupled to the container. The stage is configured to allow positioning of the container relative to the deformable fluid reservoir to so allow movement of a macrostructure (typically contained in a fluid) from the deformable fluid reservoir into the container. Further contemplated devices also include an actuator (e.g., mechanical or pneumatic) that is operably coupled to the stage to thereby allow exertion of force onto at least a portion of the deformable fluid reservoir to so cause the movement of the macrostructure from the deformable fluid reservoir into the container.

In preferred aspects of the inventive subject matter, the container comprise a porous membrane that is fluidly coupled to the fluid in the deformable fluid reservoir. For example, contemplated membranes include microporous membranes having an average pore size between 0.5 μm and 10 μm and/or where the membrane has an average pore density of between 1×10⁶ pores/cm² and 1×10⁸ pores/cm². Among other suitable membrane materials, especially suitable materials include nylon, polytetrafluoroethylene (PTFE), expanded polytetrafluoroethylene (ePTFE), polyetheretherketone (PEEK), expanded polyetheretherketone (ePEEK), polyethylene (PE), polypropylene (PP), polyvinylidene fluoride (PVDF), ethyl vinyl acetate (EVA), thermoplastic polyurethane (TPU), and polyethersulfone (PES).

While not limiting to the inventive subject matter, the deformable fluid reservoir may be removably coupled to the container, may have a volume of between 10 μL and 500 μL, and/or may include a deformable wall. Moreover, it is contemplated that suitable stages include single-container states to allow for independent operation of each container, and stage that are configured to receive and retain multiple containers (e.g., with a single actuator exerting force upon multiple deformable fluid reservoirs to increase parallel processing). Thus, the container may be configured as a single container, or as a container array (e.g., configured as a multi well filter plate). Suitable containers may also include a structure that is configured to retain a plurality of cells in a fixed position during exertion of the force, and especially preferred structures include a microfluidic channel or a cell adhesive layer.

In addition, it is contemplated that the transfection device may further include a controller that is operably coupled to the actuator to operate the actuator such that the fluid pressure in the fluid reservoir is at least 100 hPa, or at least 200 hPa, or at least 400 hPa. Furthermore, the controller may be configured to operate the actuator such that a fluid pressure in the fluid reservoir is maintained for a period of between 10 ms and 30 s.

Therefore, the inventors also contemplate a sterile and disposable assembly for transfection that comprises a container and a deformable fluid reservoir. In especially preferred assemblies, the container and the deformable fluid reservoir are configured to allow fluid coupling to each other via a porous membrane that allows movement of a macrostructure contained in a fluid from the deformable fluid reservoir into the container. Moreover, the container and deformable fluid reservoir are also configured to sealingly maintain coupling of the container to the deformable fluid reservoir at a fluid pressure of at least 50 hPa (or at least 100 hPa, or at least 200 hPa, or at least 400 hPa) in the deformable fluid reservoir.

While not limiting to the inventive subject matter, the container may be configured as a multi well filter plate and/or may further comprises a microfluidic channel or a cell adhesive layer to retain a plurality of cells in a fixed position. Additionally, it is contemplated that the deformable fluid reservoir has a fluid port to allow loading of a fluid containing a macrostructure or that the deformable fluid reservoir is prefilled with a fluid containing a macrostructure. Most typically, the container has a volume of less than 250 mL and/or the deformable fluid reservoir has a volume of less than 250 μL.

Various objects, features, aspects and advantages of the inventive subject matter will become more apparent from the following detailed description of preferred embodiments, along with the accompanying drawing figures in which like numerals represent like components.

BRIEF DESCRIPTION OF THE DRAWING

FIG. 1A is a schematic overview of one exemplary transfection device according to the inventive subject matter.

FIG. 1B provides a detail view of an exemplary stage and container of the device of FIG. 1A.

FIG. 1C provides a detail view of an exemplary deformable fluid reservoir (upper panel) and container engaged with the reservoir (lower panel) of the device of FIG. 1A.

FIG. 2 illustrates another exemplary configuration of an assembly of the container and deformable fluid reservoir according to the inventive subject matter.

FIG. 3 illustrates an exemplary detail in which a pneumatic actuator (left panel) or a mechanical actuator (right panel) interacts with the deformable fluid reservoir.

FIG. 4 is a graph illustrating exemplary deflection of a wall in the deformable fluid reservoir as a function of type and force applied to the wall.

FIG. 5 is a graph depicting colony numbers as a function of pump pressure.

FIG. 6 is a graph depicting transfection frequency as a function of transfection method.

FIG. 7 is a graph depicting colony forming frequency after delivery of mitochondria as function of types of substrate and pore size.

FIG. 8 is a graph depicting colony forming frequency after delivery of mitochondria as function of pore density.

FIG. 9 is a graph depicting pore density-normalized colony numbers as a function of membrane materials and pore size.

FIG. 10 is a graph depicting transfection rates for DNA (upper panel) and RNA (lower panel) using nucleic acid lipoplexes indicating success of transfection of DNA (upper panel) and RNA lipoplexes (lower panel) using contemplated methods relative to known top loading techniques.

FIGS. 11A and 11B are graphs depicting colony numbers using contemplated devices and methods as a function of mitochondria material (upper panel) and mitochondria pretreatment (lower panel).

FIGS. 12A and 12B are graphs depicting transfection rates for delivery conditions (upper panel) and cell pretreatment (lower panel) using contemplated methods and devices.

FIGS. 13A and 13B are graphs depicting transfection rates (upper panel) and GFP intensities (lower panel) as a function of transfection agents using contemplated methods and devices.

DETAILED DESCRIPTION

The inventors have discovered methods and devices to deliver various macrostructures, including cellular components, cell organelles, and bacteria into a target cell in a non-disruptive manner. Moreover, contemplated methods and devices allow a large number of target cells to be modified, thus allowing for high-throughput transfection. Most notably, the inventors have also discovered that a relatively moderate mechanical force applied to macrostructures and target cells will lead to uptake of the macrostructures into the cells in a non-destructive manner, most likely via active endocytosis.

Therefore, in one aspect of the inventive subject matter a transfection device for delivery of various macrostructures (e.g., mitochondria, bacteria, DNA/RNA lipoplexes, etc.) into target cells is contemplated in which an actuator provides a force that acts upon the macrostructures (typically in solution) and the cells such that the macrostructures that are proximal to the cells are taken up into the cells. In especially preferred transfection devices, movement of the cells is at least temporarily restrained (or adherent cells are employed), and the cells are initially separated from the macrostructures by a porous membrane, wherein the macrostructures are contained in a deformable fluid reservoir. Upon exertion of a force onto the deformable fluid reservoir, the macrostructures pass across the pores to the at least temporarily immobilized cells, triggering uptake of at least some of the macrostructures into the cells.

For example, contemplated transfection devices will typically have a stage configured to receive and retain a container to which a deformable fluid reservoir is fluidly coupled. The stage is further configured to allow positioning of the container relative to the fluid reservoir such as to allow movement of macrostructures contained in a fluid from the deformable fluid reservoir into the container. In most preferred aspects, movement is facilitated via a porous membrane. The transfection device will also include an actuator that is operably coupled to the stage and that is configured to allow exertion of a force onto at least a portion of the deformable fluid reservoir in an amount effective to cause the movement of the macrostructure from the deformable fluid reservoir into the container. As used herein, and unless the context dictates otherwise, the term “coupled to” is intended to include both direct coupling (in which two elements that are coupled to each other contact each other) and indirect coupling (in which at least one additional element is located between the two elements). Therefore, the terms “coupled to” and “coupled with” are used synonymously.

One exemplary device is schematically illustrated in the detail view of FIG. 1A. Here, the device 100 has a stage 110 that is configured to removably retain one or more containers 112 that contain cells for transfection. In the example of FIG. 1A, the bottom surface of container 112 includes a porous membrane 114 and the lower portion of the container 112 is configured such as to sealingly engage with the a mating portion of the deformable fluid reservoir 120 as is shown in more detail below. Base plate 130 is disposed below the deformable fluid reservoir 120 and includes one or more pistons 132. Actuator 140 is disposed below base plate 130 and exerts an upwards force onto base plate 130 such that the pistons engage with a lower surface of the deformable fluid reservoir 120 as is also shown in more detail below. FIG. 1B provides a more detailed view of an exemplary stage 110. Here, the stage includes a receiving plate 113 having one or more openings to removably receive one or more containers 112 that have a porous membrane 114 at their lower surface. Container 112 is retained in the openings of the receiving plate via cover plate 111 such that when the actuator 140 exerts force upon the deformable fluid reservoir 120, the container remains in the same position relative to the stage.

The upper panel of FIG. 1C shows a detail view of an exemplary deformable fluid reservoir 120 where the deformable fluid reservoir comprises multiple layers. Here, the top layer 121 comprises a pliable material that allows for sealing and retaining engagement with the container (see lower panel). While not limiting to the inventive subject matter, the top layer will have cutouts and have a thickness that is selected such as to provide sufficient volume for a fluid that contains the macrostructures when the container is sealingly engaged with the deformable fluid reservoir. Thus, it should be appreciated that the fluid that contains the macrostructures is contained by both, the deformable fluid reservoir and the porous membrane of the container. Middle layer 122 is typically made from a deformable material that together with the cutouts in the top layer forms a well for the liquid containing the macrostructures. In especially preferred aspects, the material for the middle layer is selected such as to allow a compressive force to act on the middle layer to thereby produce a fluid pressure of at least 50 hPa, or at least 100 hPa, or at least 200 hPa, or at least 400 hPa when the container is sealingly engaged with the container.

The bottom layer 123 of the deformable fluid reservoir typically provides a rigid support platform for the middle and top layers and will typically include one or more openings for the actuator or piston 132 of the base plate 130.

The lower panel of FIG. 1C schematically illustrates a container 112 sealingly engaged (typically via press fit) with the top layer 121 such that the porous membrane 114 at the bottom of the container 112 is in fluid contact with the suspension 170 formed from the fluid and the macrostructures. Direct or indirect actuation (e.g., via piston 132) exerts mechanical force 141 onto the deformable middle layer 122. Middle layer and top layer are both supported by bottom layer 132. Thus, it should be appreciated that by providing a force onto the pliable middle layer, pressure in the fluid space defined by the middle layer, the top layer, and the porous membrane increases, leading to migration of the macrostructures through the pores across the porous membrane into the container and cells. In the example of FIG. 1C, the cells are retained at the bottom of the container (i.e., on the top side of the porous membrane, not shown) by a thin layer of CELL-TAK™ adhesive (polyphenolic proteins extracted from the marine mussel. Mytilus edulis, commercially available from Corning Inc., Bedford, Mass.).

Another exemplary device is schematically shown in the detail view of FIG. 2 where the container 212 is configured as a well of a multi well plate. The deformable fluid reservoir in this device comprises a frame portion 225 that helps retain porous membrane 214. Also coupled to the frame portion 225 is a deformable bottom 226 of the reservoir. Thus, as noted previously, the porous membrane and a deformable portion of the fluid reservoir define the fluid reservoir that contains the macrostructure, and pressure onto the deformable portion will result in passage of the macrostructures through the pores of the porous membrane to the cells. Most typically, the fluid reservoir is preloaded, but it should be noted that the fluid reservoir may also include one or more fill and vent ports to fill the fluid reservoir before use.

With respect to suitable containers it is generally contemplated that the container may be made from a variety of materials, however, especially preferred materials are sterilizable by heat, radiation, and/or chemical treatment. Therefore, appropriate materials include various polymers (e.g., PE, PET, HDPE, PDMS, PC, etc.), glass, metals, and all reasonable combinations hereof. Regardless of the material, it is further preferred that the container has a shape suitable for receiving and retaining mammalian cells and that the container is configured to allow culturing of the cells. Thus, containers contemplated herein will typically have a volume between 0.1 mL and 250 mL, or even higher. For example, where the container is configured as a multi well plate, suitable volumes will be between 0.1 and 20 mL. On the other hand, where the container is configured as a culture flask or culture beaker, suitable volumes will be between 10 and 250 mL, or between 250 and 1000 mL. Thus, the shape of suitable containers is typically not limited and shaped considered suitable for use in conjunction with the teachings presented herein include cup shapes, cell culture flask shapes, box shapes, cylinder shapes, Petri dish shapes, etc. In still further contemplated aspects, containers will preferably be single use and disposable containers that are sterilized.

The recitation of ranges of values herein is merely intended to serve as a shorthand method of referring individually to each separate value falling within the range. Unless otherwise indicated herein, each individual value is incorporated into the specification as if it were individually recited herein. All methods described herein can be performed in any suitable order unless otherwise indicated herein or otherwise clearly contradicted by context. The use of any and all examples, or exemplary language (e.g. “such as”) provided with respect to certain embodiments herein is intended merely to better illuminate the invention and does not pose a limitation on the scope of the invention otherwise claimed. No language in the specification should be construed as indicating any non-claimed element essential to the practice of the invention.

Regardless of the particular shape and volume, it is contemplated that the container will comprise (or be fluidly coupled to) at least one portion of a surface that includes the porous membrane. In most cases, the porous membrane forms at least a portion of a bottom surface of the container. There are numerous porous membrane known in the art, and all porous membranes are deemed suitable so long as such porous membranes are able to support and/or retain cells during transfection. For example, contemplated porous membranes may be made from various materials, including nylon, polytetrafluoroethylene (PTFE), expanded polytetrafluoroethylene (ePTFE), polyetheretherketone (PEEK), expanded polyetheretherketone (ePEEK), polyethylene (PE), polypropylene (PP), polyvinylidene fluoride (PVDF), ethyl vinyl acetate (EVA), thermoplastic polyurethane (TPU), or polyethersulfone (PES). In further contemplated aspects, the membrane will typically be relatively thin and may therefore have a thickness of between 1 μm and 1 mm, or between 3 μm and 0.5 mm, or between 5 μm and 250 μm. Viewed form a different perspective, suitable membranes will generally have a thickness of at least 1 μm, or at least 3 μm, or at least 5 μm, or at least 10 μm. It should be noted that the membrane thickness will also be determined at least in part by the pressure applied to the deformable fluid reservoir. However, support structures (e.g., support grid or mesh) to avoid membrane failure are also expressly contemplated herein.

The average pore size of the porous membrane will typically depend on various factors and the size and/or flexibility of the macrostructure will be particularly relevant. Therefore, it is contemplated that the average or median pore size of the porous membrane ranges from about 50 nm, or from about 100 nm, or from about 200 nm, or from about 300 nm, or from about 400 nm, or from about 500 nm, or from about 600 nm, or from about 700 nm, or from about 800 nm, or from about 900 nm, or from about 1 μm up to about 30 μm, or up to about 20 μm, or up to about 15 μm, or up to about 10 μm, or up to about 8 μm, or up to about 5 μm. In certain embodiments the median or average pore size in the porous membrane is about 1 μm or about 3 μm, or about 5 μm or about 10 μm, or about 15 μm. The term ‘about’, when used in conjunction with a numeral refers to a range spanning +/−10%, inclusive, around that numeral. For example, the term ‘about 10 μm refers to a range of 9 to 11 μm, inclusive.

With respect to the pore density of the membrane it is contemplated that the density will be sufficiently high such that on average a cell will cover (or be located above) at least one pore, or at least two pores, or at least 3 pores, or at least 4 pores, or at least 5 pores, or at least 10 pores. Thus, the pore density in some embodiments will be between about 1×10⁵ pores/cm² to about 1×10⁷ pores/cm², or between about 5×10⁵ pores/cm² to about 5×10⁶ pores/cm², or at least 1×10⁵ pores/cm², or at least 1×10⁶ pores/cm², or at least 1×10⁷ pores/cm². Viewed from a different perspective, the porous membrane comprises in some embodiments about a 1-10 μm diameter average pore size at about 1×10⁶-10⁷ pores/cm².

In still further contemplated aspects of the inventive subject matter, additional elements may be included with the container and membrane to at least temporarily retain cells in a fixed position on the porous membrane. For example, additional elements may include microfluidic channels though which the cells may be fed to/maintained on the membrane, a mesh to retain the cells on the membrane, or the membrane may be coated with an adhesive that temporarily retains the cells on the membrane. There are various adhesives known in the art, and all of them are deemed suitable for use herein, including collagen matrices, CELL-TAK™ adhesive, poly-L-lysine, extracellular matrix proteins (e.g., collagen, fibronectin, laminin, etc.), or other adherents. Alternatively, it is noted that where adherent cells are used, no additional elements to retain the cells may be needed.

Deformable fluid reservoirs contemplated herein will generally have a volume suitable for retaining sufficient macrostructures to transfect a desirable number of cells. Consequently, depending on the cell number, the transfection efficiency, surface area of the porous membrane, and other factors, the volume of the deformable fluid reservoir may vary considerably. However, it is generally contemplated that the volume will be between about 10 μL and 5 mL (in some cases even higher), or between about 100 μL and 1 mL, or between about 50 μL and 500 μL, or between about 100 μL and 1000 μL. Similarly, the shape of the deformable fluid reservoir may vary considerably but it is generally contemplated that the particular shape will be at least in part determined by the shape of the container and the size of the porous membrane. Consequently, it is contemplated that the deformable portion will preferably a wall or wall portion, which may be homogenously deformed or locally, or that the deformable portion is replaced by a movable wall or wall portion (e.g., configured as a plunger). Alternatively, the entire deformable fluid reservoir may also be compressible. Moreover, it is contemplated that the deformable fluid reservoir will sealingly engage with the container such that the macrostructures will be able to flow from the reservoir (typically within the fluid) into the container and to the cells on the porous membrane. In especially preferred aspects, sealing engagement of the deformable fluid reservoir with the container is maintained at pressures in the deformable fluid reservoir of at least 50 hPa, at least 100 hPa, at least 200 hPa, at least 400 hPa, at least 800 hPa. Viewed from a different perspective, the sealing engagement may be maintained at pressures between 1 and 1000 hPa, between 10 and 800 hPa, between 50 and 600 hPa, or between 100 and 1000 hPa.

In still further contemplated aspects of the inventive subject matter, the deformable fluid reservoir may be coupled to or include or one or more ports through which a fluid containing the macrostructures can be introduced, preferably using sterile techniques and sterile adapters (e.g., Luer lock adapters). Where desirable, vent and/or discharge ports may be included to facilitate loading and unloading of the deformable fluid reservoir. Most typically, the deformable fluid reservoir will be removable. However, permanently affixed deformable fluid reservoirs are also contemplated (in such case, the reservoirs may be prefilled with a fluid and macrostructures).

Among other things, macrostructures suitable for use herein will include cell organelles (e.g., nucleus, mitochondria, chloroplast, ribosomes, etc.), viruses and microorganisms (e.g., gram⁺ and gram⁻ bacteria, etc.), various macromolecules, and especially recombinant and natural nucleic acids alone or in combination with a transfection agent (e.g., native, synthetic or artificial chromosomes, miRNA, siRNA, plasmids, double minute chromosomes, etc.), proteins and/or protein complexes, and drug delivery particles.

Therefore, the type of fluids appropriate for storage and movement may vary considerably, but it is generally preferred that the fluids include physiologically acceptable solutions (e.g., isotonic and buffered solutions), growth media, etc. Examples of suitable fluids include experimental buffer, PBS, DMEM, HBSS, Opti-MEM, DMEM without Ca2+, or other media amenable to the nature of cargo material. The macrostructures in the fluid can also comprise one or more lipid carriers. Example lipid carries can Lipofectamine, Transfectace, Transfectam, Cytofectin, DMRIE, DLRIE, GAP-DLRIE, DOTAP, DOPE, DMEAP, DODMP, DOPC, DDAB, DOSPA, EDLPC, EDMPC, DPH, TMADPH, CTAB, lysyl-PE, DC-Cho, -alanyl cholesterol; DCGS, DPPES, DCPE, DMAP, DMPE, DOGS, DOHME, DPEPC, Pluronic, Tween, BRU, plasmalogen, phosphatidylethanolamine, phosphatidylcholine, glycerol-3-ethylphosphatidylcholine, dimethyl ammonium propane, trimethyl ammonium propane, diethylammonium propane, triethylammonium propane, dimethyldioctadecylammonium bromide, a sphingolipid, sphingomyelin, a lysolipid, a glycolipid, a sulfatide, a glycosphingolipid, cholesterol, cholesterol ester, cholesterol salt, oil, N-succinyldioleoylphosphatidylethanolamine, 1,2-dioleoyl-sn-glycerol, 1,3-dipalmitoyl-2-succinylglycerol, 1,2-dipalmitoyl-sn-3-succinylglycerol, 1-hexadecyl-2-palmitoylglycerophosphatidylethanolamine, palmitoylhomocystiene, N,N′-Bis (dodecyaminocarbonylmethylene)-N,N′-bis((-N,N,N-trimethylammoniumethyl-aminocarbonylmethylene)ethylenediamine tetraiodide; N,N″-Bis(hexadecylaminocarbonylmethylene)-N,N′,N″-tris((-N,N,N-trimethylammonium-ethylaminocarbonylmethylenediethylenetriamine hexaiodide; N,N′-Bis(dodecylaminocarbonylmethylene)-N,N″-bis((-N,N,N-trimethylammoniumethylaminocarbonylmethylene)cyclohexylene-1,4-diamine tetraiodide; 1,7,7-tetra-((-N,N,N,N-tetramethylammoniumethylamino-carbonylmethylene)-3-hexadecylaminocarbonyl-methylene-1,3,7-triaazaheptane heptaiodide; or N,N,N′,N′-tetra((-N,N,N-trimethylammonium-ethylaminocarbonylmethylene)-N′-(1,2-dioleoylglycero-3-phosphoethanolaminocarbonylmethylene)diethylenetriamine tetraiodide.

Actuators include all devices capable of compressing the deformable fluid reservoir to an extent that the macrostructures will move through the pores to the cells. Thus, suitable actuators will include mechanical actuators (e.g., piston, screw drive, solenoid, etc.), hydraulic actuators (e.g., using aqueous fluid or oil), or pneumatic actuators (e.g., femtojet), even manual actuators. Therefore, it should also be appreciated that the actuator may be replaced by a pressurization device that directly pressurizes the contents of the deformable fluid reservoir, and suitable devices may include fluid pumps and pneumatic pumps. In still other aspects of the inventive subject matter, the compression is directly performed on the cells and may this include planar pressure elements, rollers, etc., or pressurized fluid droplets enclosing macrostructures may be accelerated onto the cells (e.g., via fluid jet devices, or inkjet print heads, etc.), typically at pressures of less than 1000 hPa.

In still further preferred aspects, the actuator operation is performed via a controller that is configured to move the actuator such that movement of the actuator effects deformation of the deformable fluid reservoir, and with that pressurizes the fluid. The inventors have discovered, as is shown in more detail below, that cell transfection is particularly effective in a relatively small range of conditions. In especially preferred aspects, the controller is configured to apply pressure via the actuator for a period of time ranging from about 10 ms to about 30 s, or from about 20 ms to about 15 s, or from about 20 ms to about 300 ms. Thus, the controller will typically operate the plunger such that the deformable fluid reservoir is pressurized for at least about 10 ms, at least 25 ms, at least 50 ms, at least 100 ms, or at least 500 ms, or at least 1 s, or at least 5 s, but in most cases less than 10 s, or less than 20 s, or less than 30 s, or less than 60 s. In some instances, pressurization may also last about 1 min, or up to about 1.5 min, or up to about 2 min, or up to about 2.5 min, or up to about 5 min. Most typically, however, the controller will be configured to effect pressurization for a period of time ranging from about 10 ms up to about 500 ms.

The controller is also preferably configured such as to effect pressurization of the fluid in the deformable fluid to a pressure of at least 10 hPa, at least 20 hPa, at least 50 hPa, at least 100 hPa, at least 200 hPa, at least 400 hPa, or at least 800 hPa. Therefore, suitable pressure ranges effected by the controller will be between 10 hPa and 1000 hPa, or between 20 hPa and 800 hPa, or between 40 hPa and 400 hPa, or between 50 hPa and 500 hPa. Additionally, it should be appreciated that the slope of pressure increase may vary considerably, and in most cases maximum pressure levels will be attained within less than 10 s, or less than 5 s, or less than 1 s, or less than 500 ns, or less than 250 ms. Of course, it should be recognized that the controller may also be programmable to a particular profile having a predetermined maximum pressure, predetermined pressure duration, and/or predetermined time to maximum pressure. Where feedback mechanisms are contemplated, it is typically preferred that the controller receives information of at least one pressure sensor in the device, typically located in the deformable fluid reservoir.

FIG. 3 schematically and exemplarily illustrates two different modes of actuation as discussed above. On the left panel, the actuator 340A is a pneumatic actuator that provides pressurized air into the deformable fluid reservoir that has a flexible membrane 322A that forms part of the fluid reservoir above (container not shown). In such embodiment, the deformable portion is part of an inflatable chamber, the top of which forms the bottom of the fluid reservoir. Similarly, on the right panel, the actuator 340B is a solenoid actuator that directly presses against the deformable membrane 322B, the top of which forms the bottom of the fluid reservoir. As will be readily appreciated, the type of actuator and controller settings all fine-tuned pressure increases as can be taken from FIG. 4. Here, the graph depicts deflection kinetics of the deformable portion of the fluid chamber as a function of operation and type of actuator.

Experimental Data

The following experiments provide exemplary guidance on certain aspects of the device and methods of use, but should not be construed to be limiting in any manner. Unless specified otherwise, all transfection experiments were performed with a device according to FIG. 1A using the following typical experimental set-up:

A solenoid actuator is affixed to the bottom of the deformable fluid reservoir. The fluid reservoir is made by stacking and bonding polydimethylsiloxane (PDMS) layers creating a 100 uL void for cargo loading. Recipient cells are cultured or immobilized on a porous membrane and then stacked on top of the fluid reservoir. For transfection, the solenoid actuator is activated to deform the fluid reservoir and subsequently pump the cargo suspension into the recipient cells.

More specifically, FIG. 5 exemplarily illustrates suitable pump pressures to achieve transfection of mammalian cells with mitochondria, while FIG. 6 provides a comparison for transfection efficiency using the devices presented herein vis-à-vis conventional transfection methods. FIG. 5 presents graph that shows the number of successful mitochondria transfected colonies generated at various pressures. When the assembly is not clamped or locked down, no successful colonies were generated. Interestingly, at ambient pressure where the device is only under clamp pressure transfection occurs. Thus, it should be appreciated that the devices contemplated herein are able to achieve successful transfection at pressures that are at about ambient pressure, at least 50 hPa above ambient pressure, at least 100 hPa above ambient pressure, 200 hPa above ambient pressure, or even at least 400 hPa above ambient pressure. FIG. 6 illustrates a comparison of the transfection device contemplated herein with various other techniques. As can be readily seen from the graph, the device according to the inventive subject matter is capable of successfully transfecting cells with mitochondria as compared to other known techniques that failed to deliver mitochondria at any significant fraction. The data in FIG. 6 were generated using a PASTe device that has a porous substrate with 3 μm pores.

The colony forming frequency for mitochondria delivery (Fc) is calculated by dividing the number of transfected cells (Nt) that successfully grow colonies by number of initial cells (Ni); thus Fc=Nt/Ni. Interestingly, just after delivery, both the PASTe device and co-incubation delivered mitochondria with an efficiency of about 80%. However, only the PASTe device generated transfected cells capable of growing colonies that remained alive and inherited the transfected mitochondria.

FIG. 7 shows exemplary results for various porous materials that can be used with the devices according to the inventive subject matter. As can be readily seen from the graph, a broad spectrum of porous substrates including at least PC, PET, deformable membranes, or even rigid substrates such as silicon can be successfully employed. These substrates are readily available from manufactures including CORNING®, BECTON DICKENSON®, and WHATMAN®. Furthermore, the graph also indicates that transfection with mitochondria is successful with a range pore sizes from 0.4 μm through at least 8 μm. Most notably, the data also indicate that mitochondria delivery via contemplated transfection devices can have a success frequency that is at least 1×10⁻⁵, more preferably at least 8×10⁻⁵, even more preferably at least 1×10⁻⁴, or yet more preferably at least 4×10⁻⁴. Liposome delivery has successfully achieved efficiencies of at least 15%, including at least 70%.

FIG. 8 presents data using pore density for the substrates from FIG. 7. As can be readily taken from the data, acceptable pore densities (pores/cm²) be a least 1×10⁴ pores/cm², at least 1×10⁵ pores/cm², at least 4×10⁶ pores/cm², at least 1×10⁷ pores/cm², or even at least 1×10⁸ pores/cm². When the data from FIGS. 7 and 8 are combined an indication can be obtained which substrate will generate the most viable colonies as shown in FIG. 9 in which colony frequency has been normalized by pore density. At least with respect to mitochondria delivery and the set of substrates tested, an 8 μm pore size having relatively low pore density yields the most viable colonies at least for the experiments run.

FIG. 10 exemplarily shows results for transfection using DNA and RNA lipoplexes in conjunction with the devices contemplated herein as well as with traditional top transfection in which DNA and RNA lipoplexes were applied on top of MDCK cells. The delivered lipoplex contains green fluorescent protein (GFP) encoding DNA or RNA. As a result, successfully transfected cells are indicated by their GFP expression. Cell mortality after transfection is measured by propidium iodine (PI) staining. Percentage of PI positive cells represents the dead cell population. Cells were plated on day 0 and transfection was carried out on day 1, 2 and 3 respectively. PASTe yielded higher transfection rate than traditional applying lipoplex to top of the cells in all experiments, especially for higher cell densities (day 3). The PASTe approach (using a device as shown in FIG. 1) used a 1 μm pore substrate and a 3 μm pore substrate, and it is readily apparent that PASTe devices outperformed the traditional techniques.

The inventors further conducted experiments to investigate the influence of actuator speed on transfection efficiency. As can be seen from the Table below, transfection efficiency with mitochondria is a function of actuator speed.

Cell density pump speed after delivery Colony # with Pump method (mm/s) (per uL) delivered mtDNA Solenoid 100 39 252 Pneumatic pump 10 53.6 135 Stepper motor 2 86.3 29 Stepper motor 0.1 76.4 3

In contrast, the following table below indicates the results for DNA Lipoplex PASTe as a function of pumping speeds. As can be readily seen, where transfection used nucleic acids, transfection efficiency is not materially affected b actuator speed.

pump speed GFP expression Median GFP Pump method (mm/s) (%) intensity Solenoid 100 29.3 12,256 Femtojet 10 41.4 11,421 Stepper 1 39.6 11,944 Top down — 32.6  3,346

To further investigate the role of mitochondria status in cell transfection, the inventors compared fresh isolated mitochondria, previously frozen mitochondria, and mtDNA using the devices according to the inventive subject matter. Here, FIGS. 11A and 11B illustrate that the state of the isolated mitochondria is not critical for transfection results, nor that transfection efficiency is critically affected by various mitochondria inhibitors (CCCP: drug to dissipate mitochondrial membrane potential; Oligomycin: inhibits mitochondrial respiration; R6G: inhibits mitochondrial respiration). Further experiments, as depicted in FIGS. 12A and 12B, suggest that the uptake of mitochondria is an active and energy dependent process. Here, transfection efficiency is significantly lower at lower temperatures. Amiloride is a macropinocytosis inhibitor. Genistein and Cyclodextrin are caveolae mediated endocytosis inhibitors, and Chlorpromazine is a clathrin mediated endocytosis inhibitor.

FIGS. 13A and 13B illustrate exemplary results from transfection of human skin fibroblasts comparing various transfection agents and methods for RNA. GFP mRNA was complexed with Lipofectamine 2000, Lipofectamine RNAiMAX and Stemfect transfection reagents according to the manufacturer's protocols prior to delivery into the cells via top transfection or PASTe. As is readily apparent not all transfection agents had the same effect, and the best agent tested was LF2k (Lipofectamine 2000) for PASTe devices, while stemfect was best for top transfection.

Lastly, the inventors employed contemplated devices to increase efficiency and reproducibility for reprogramming induced pluripotent stem (iPS) cell. Here, mRNA cocktails containing reprogramming factors OCT4, KLF4, C-MYC, SOX2 and LIN28A were complexed with different transfection reagents according to manufacturer's protocol and delivered into human skin fibroblasts daily over a course of 2 weeks (Ref). At the end of the two weeks, successfully reprogrammed iPS colonies expressing pluripotent markers were counted and compared between different experimental conditions. (Ref: P. K. Mandel and D. J. Rossi. Reprogramming human fibroblasts to pluripotency using modified mRNA. Nature Protocols 8, p. 568-582, 2013). As can be taken from the results in the table below, contemplated devices and methods were superior to traditional transfection using transfection agents without the device.

Well #1 Well #2 Well #3 Well #4 PASTe LF2k RNAiMAX LF2k (ramp) LF2k + miRNA iPS colony 29 21 23 73 # at D 14 Well #1 Well #2 Well #3 Well #4 Top LF2K RNAiMAX Stemfect Stemfect + miRNA iPS colony 0 3 0 0 # at D 14

Thus, it should be noted that mitochondria (and bacteria) PASTe transfection experiments have shown that (1) transfection efficiency is sensitive to pumping speed, (2) donor mitochondria will typically not require intact membrane potential or respiration, and (3) transfection can be inhibited by macropinocytosis inhibitors. In contrast. RNA/DNA Lipoplex PASTe transfection experiments have shown that (1) efficiency is insensitive to pumping speed (preferably performed at low speed). (2) process works best in adherent cells, and (3) process works best with Lipofectamine 2000.

The following discussion provides many example embodiments of the inventive subject matter. Although each embodiment represents a single combination of inventive elements, the inventive subject matter is considered to include all possible combinations of the disclosed elements. Thus if one embodiment comprises elements A. B, and C, and a second embodiment comprises elements B and D, then the inventive subject matter is also considered to include other remaining combinations of A. B, C, or D, even if not explicitly disclosed.

It should be apparent to those skilled in the art that many more modifications besides those already described are possible without departing from the inventive concepts herein. The inventive subject matter, therefore, is not to be restricted except in the spirit of the appended claims. Moreover, in interpreting both the specification and the claims, all terms should be interpreted in the broadest possible manner consistent with the context. In particular, the terms “comprises” and “comprising” should be interpreted as referring to elements, components, or steps in a non-exclusive manner, indicating that the referenced elements, components, or steps may be present, or utilized, or combined with other elements, components, or steps that are not expressly referenced. Where the specification claims refers to at least one of something selected from the group consisting of A, B. C . . . and N, the text should be interpreted as requiring only one element from the group, not A plus N, or B plus N, etc. 

1-15. (canceled)
 16. A sterile and disposable assembly for transfection, comprising: a container and a deformable fluid reservoir, wherein the container and the deformable fluid reservoir are configured to allow fluid coupling to each other via a porous membrane that allows movement of a macrostructure contained in a fluid from the deformable fluid reservoir into the container; and wherein the container and deformable fluid reservoir are configured to sealingly maintain coupling of the container to the deformable fluid reservoir at a fluid pressure of at least 50 hPa in the deformable fluid reservoir.
 17. The sterile and disposable assembly of claim 16 wherein the container is configured as a multi well filter plate.
 18. The sterile and disposable assembly of claim 16 wherein the container further comprises a microfluidic channel or a cell adhesive layer configured to retain a plurality of cells in a fixed position.
 19. The sterile and disposable assembly of claim 16 wherein the deformable fluid reservoir has a fluid port configured to allow loading of a fluid containing a macrostructure or wherein the deformable fluid reservoir is prefilled with a fluid containing a macrostructure.
 20. The sterile and disposable assembly of claim 16 wherein the container has a volume of less than 250 mL and wherein the deformable fluid reservoir has a volume of less than 250 μL. 